JP2765602B2 - Auto drift cancellation circuit of ECG analyzer - Google Patents
Auto drift cancellation circuit of ECG analyzerInfo
- Publication number
- JP2765602B2 JP2765602B2 JP3284464A JP28446491A JP2765602B2 JP 2765602 B2 JP2765602 B2 JP 2765602B2 JP 3284464 A JP3284464 A JP 3284464A JP 28446491 A JP28446491 A JP 28446491A JP 2765602 B2 JP2765602 B2 JP 2765602B2
- Authority
- JP
- Japan
- Prior art keywords
- electrocardiogram
- differential amplifier
- signal
- auto
- circuit
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
- Amplifiers (AREA)
Description
【0001】[0001]
【産業上の利用分野】本発明は携帯用心電図解析装置の
心電図入力方法に関し、特にオートドリフトキャンセル
回路に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an electrocardiogram input method for a portable electrocardiogram analyzer, and more particularly to an auto drift cancel circuit.
【0002】[0002]
【従来の技術】従来の携帯用心電図解析装置は、被検者
が装着した電極から導出される微少な心電図信号を検出
し増幅するために、心電図入力部は差動アンプを有し、
この差動アンプにより5倍程度に増幅された心電図信号
は、自域周波数成分(0.05Hz以下)をカットするた
めの1次のフィルタを通過後、次段のメインアンプによ
り250倍程度まで増幅されA/D変換器に入力されて
いた。2. Description of the Related Art A conventional portable electrocardiogram analyzing apparatus has a differential amplifier in an electrocardiogram input section in order to detect and amplify a small electrocardiogram signal derived from an electrode worn by a subject.
The electrocardiogram signal amplified by about 5 times by this differential amplifier passes through a primary filter for cutting its own frequency component (0.05 Hz or less), and is then amplified to about 250 times by the next stage main amplifier. And input to the A / D converter.
【0003】[0003]
【発明が解決しようとする課題】しかしながら、従来の
携帯用心電図解析装置では、バッテリー駆動(通常は単
3電池4本程度)のため、装置のアンプ部の動作中の電
源電圧は4〜6V程度であり、差動アンプの増幅度を5
倍とすると、ダイナミックレンジは、せいぜい、入力換
算で800〜1000mV程度しかないため、体動や電極
パッドの動きなどのアーチファクトにより、差動アンプ
への直流入力分が急激に変化した場合に、差動アンプの
出力が飽和してしまい誤解析の要因となるという問題点
があった。However, in the conventional portable electrocardiogram analyzer, the power supply voltage during the operation of the amplifier section of the device is about 4 to 6 V because the battery is driven (usually about 4 AA batteries). And the amplification degree of the differential amplifier is 5
If it is doubled, the dynamic range is at most about 800 to 1000 mV in terms of input at most, so if the DC input to the differential amplifier changes suddenly due to artefacts such as body movement and electrode pad movement, There has been a problem that the output of the dynamic amplifier is saturated, which causes erroneous analysis.
【0004】また従来の心電入力回路では、1次のハイ
パスフィルタで32秒の時定数を低域のカットオフ周波
数が0.05Hzを実現しているため、アンプ入力の変動
後に、仮に入力が安定したとしても、心電信号が基線レ
ベルに戻るまでは6秒以上またなければならなかった。
また、0.05Hz以上の低周波成分を有するドラフトは
キャンセルすることができなかった。Further, in the conventional electrocardiographic input circuit, the time constant of 32 seconds is realized by the first-order high-pass filter, and the cutoff frequency of the low band is realized at 0.05 Hz. Even if stabilized, it had to take more than 6 seconds for the ECG signal to return to baseline levels.
Further, a draft having a low frequency component of 0.05 Hz or more could not be canceled.
【0005】[0005]
【課題を解決するための手段】本発明によれば、心電図
信号を検出して増幅する差動アンプを有する心電図解析
装置のオートドリフトキャンセル回路において、前記心
電図信号に基づいて、前記差動アンプに、当該差動アン
プの入力レンジ内に入るように、所定のタイミングにお
ける前記心電図信号の基線レベルに基づいて、バイアス
を印加するバイアス手段を備えていることを特徴とする
心電図解析装置のオートドリフトキャンセル回路が得ら
れる。According to the present invention, there is provided an auto drift canceling circuit of an electrocardiogram analyzing apparatus having a differential amplifier for detecting and amplifying an electrocardiogram signal. At a predetermined timing so as to fall within the input range of the differential amplifier .
Bias based on the baseline level of the ECG signal
And an auto-drift canceling circuit of the electrocardiogram analyzing apparatus, characterized in that the auto-drift canceling circuit is provided with a bias means for applying a bias voltage .
【0006】[0006]
【0007】また、本発明によれば、被検者に装着した
電極から導出される心電図信号を検出して増幅する差動
アンプと、前記心電図信号をA/D変換するためのA/
D変換器と、 該A/D変換器により得られた変換デー
タからR波を検出し、R−Rインターバルから心電図信
号の基線時のタイミングを算出するR波検出部と、該R
波検出部で得られたタイミングにおける心電図信号の基
線レベルを、前記差動アンプの入力レンジの中心にバイ
アスする直流バイアス回路と、該バイアス回路へのバイ
アス電圧を出力するD/A変換器とを備えていることを
特徴とする心電図解析装置のオートドリフトキャンセル
回路が得られる。[0007] According to the present invention, the subject wears the subject.
Differential to detect and amplify ECG signals derived from electrodes
An amplifier and an A / D converter for A / D converting the electrocardiogram signal.
A D converter and conversion data obtained by the A / D converter.
Data from the R-R interval
An R-wave detector for calculating the timing of the signal at the time of the baseline;
Of the ECG signal at the timing obtained by the wave detector
Line level to the center of the input range of the differential amplifier.
DC bias circuit and bias to the bias circuit.
An auto-drift canceling circuit for an electrocardiogram analyzing apparatus, comprising: a D / A converter that outputs a bias voltage .
【0008】[0008]
【実施例】次に本発明の実施例について図面を参照して
説明する。Next, an embodiment of the present invention will be described with reference to the drawings.
【0009】図1は本発明の一実施例である。被検者が
装着した電極から導出される心電図信号を検出して増幅
する差動アンプ1の出力はメインアンプ3によりA/D
変換器4の入力レベルまで増幅される。FIG. 1 shows an embodiment of the present invention. The output of the differential amplifier 1 for detecting and amplifying an electrocardiogram signal derived from the electrode worn by the subject is A / D-converted by the main amplifier 3.
It is amplified to the input level of the converter 4.
【0010】ここで差動アンプ1の反転、非反転入力の
それぞれに入力される信号e1 ,e2 は、 e1 =v1 +E1 …(1) v1 :心電図信号成分 E1 :分極、アーチファクトによる直流分 e2 =v2 +E2 …(2) v2 :心電図信号成分 E2 :分極、アーチファクトによる直流分 (1),(2)式で表わされ、バイアス回路2の出力電
圧Vとすると作動アンプLの出力e0 は下式で表わされ
る。Here, signals e 1 and e 2 input to the inverting and non-inverting inputs of the differential amplifier 1, respectively, are e 1 = v 1 + E 1 (1) v 1 : electrocardiogram signal component E 1 : polarization DC component due to artifact e 2 = v 2 + E 2 (2) v 2 : electrocardiogram signal component E 2 : DC component due to polarization and artifact Eq. (1), (2), output voltage of bias circuit 2 Assuming V, the output e 0 of the operation amplifier L is expressed by the following equation.
【0011】 e=−R2 /R1 (v1 −v2 )−R2 /R1 (E1 −E2 )+V …(3) つまり、(3)式の第2項が差動アンプ1の出力からキ
ャンセルすべきドリフト成分と考えられるから、(3)
式第3項のバイアス回路2の出力電圧Vを可変させ
(4)式を満足するときドリフトをキャンセルする。E = −R 2 / R 1 (v 1 −v 2 ) −R 2 / R 1 (E 1 −E 2 ) + V (3) That is, the second term of the equation (3) is a differential amplifier. Since it is considered that the drift component should be canceled from the output of No. 1, (3)
The drift is canceled when the output voltage V of the bias circuit 2 in the third term of the equation is varied and the equation (4) is satisfied.
【0012】 V=R2 /R1 (E1 −E2 ) …(4) ことが可能となる。V = R 2 / R 1 (E 1 −E 2 ) (4)
【0013】また、R波検出部8でリアルタイムに検出
されたR波から心電図の基線部のタイミングTB は一般
的に(5)式で算出可能である。[0013] The timing T B of the baseline of the electrocardiogram from the R wave detected in real time R wave detector 8 is generally (5) can be calculated by the formula.
【0014】 TB (sec)=2/3TR-R (sec) …(5) ( TR-R =R−Rインターバル) 図2に示すように、R波検出部8で検出されたR検
(u)と前回のR検(u−1)からRR-R(u-1)とT
B(u-1)を算出する。[0014] T B (sec) = 2 / 3T RR (sec) ... (5) (T RR = RR interval) as shown in FIG. 2, R inspection detected by the R wave detector 8 (u) And R RR (u-1) and T from the previous R test (u-1)
Calculate B (u-1) .
【0015】Te 値はR波を検出する毎に随時、更新さ
れていく。[0015] T e value from time to time in each time of detecting the R-wave, will be updated.
【0016】従って、R波を検出してからTR 時間経過
後は、心電図信号の基線部と考えられため、この時の心
電図信号レベルと差動アンプ1の入力レンジの中心との
差分を検出することで心電図信号のドリフト成分の検出
が可能となる。[0016] Thus, elapses after detecting the R-wave T R time, since considered the baseline of the electrocardiogram signal, detecting the difference between the center of the input range of the ECG signal level and the differential amplifier 1 at this time This makes it possible to detect the drift component of the electrocardiogram signal.
【0017】図3のAに示すように、心電図信号の基線
部と差動アンプ1の入力レンジの中心との差分V(u)
を検出し、このドリフト成分をキャンセルするように図
1のバイアス回路2の出力電圧をD/A変換器で1心拍
毎に連続的に可変させる。(図3のB) 従って図3のCのようにドリフトキャンセルが可能とな
り、急激なアーチファクト等により差動アンプ1が飽和
したとしても瞬時に基線レベルまで回復させることがで
きる。As shown in FIG. 3A, the difference V (u) between the baseline of the electrocardiogram signal and the center of the input range of the differential amplifier 1 is shown.
Is detected, and the output voltage of the bias circuit 2 in FIG. 1 is continuously varied for each heartbeat by a D / A converter so as to cancel this drift component. (B in FIG. 3) Accordingly, drift cancellation is possible as shown in C in FIG. 3, and even if the differential amplifier 1 is saturated due to a sudden artifact or the like, it can be instantaneously recovered to the baseline level.
【0018】なお、5は演算処理部(CPU)であり、
R波とR波との時間的間隔及び、ドリフト成分等と基線
レベルとの距離を判断するものである。また、6はメモ
リで、心電図信号出力を一時格納するものである。Reference numeral 5 denotes an arithmetic processing unit (CPU).
The time interval between R waves and the distance between a drift component and the like and the baseline level are determined. Reference numeral 6 denotes a memory for temporarily storing an electrocardiogram signal output.
【0019】[0019]
【発明の効果】以上説明したように本発明は、体動など
のアーチファクトにより差動アンプの入力レンジを越え
るような状態でも一心拍後には、入力レンジ内に入るよ
うに、差動アンプの入力が直流バイアスされるため、ア
ーチファクトの影響を受けにくくなり、誤解析を軽減で
きるという効果を有する。As described above, according to the present invention, even if the input range of the differential amplifier exceeds the input range due to an artifact such as body motion, the input of the differential amplifier is set to be within the input range after one heartbeat. Is subjected to DC bias, so that it is less susceptible to artifacts, and has the effect of reducing erroneous analysis.
【0020】また、低域周波数成分カットのための1次
フィルタ回路が削除できるため、1次のフィルタで使用
していた高精度で大容量のコンデンサ(以下±5%程
度)と高精度高抵抗(36 MΩ±5%程度)が削除可能
となり、部品原価の低減、実装面積の削減という効果を
有する。Also, since the primary filter circuit for cutting low frequency components can be eliminated, a high-precision, large-capacity capacitor (hereafter, about ± 5%) used in the primary filter and a high-precision, high-resistance (Approximately 36 MΩ ± 5%) can be eliminated, which has the effect of reducing component costs and mounting area.
【図1】本発明の一実施例のブロック図である。FIG. 1 is a block diagram of one embodiment of the present invention.
【図2】TB とTR-R の関係を示す図である。FIG. 2 is a diagram showing a relationship between T B and T RR .
【図3】ドリフトキャンセル方法の一実施例である。FIG. 3 is an embodiment of a drift cancellation method.
1 差動アンプ 2 直流バイアス回路 3 メインアンプ 4 A/D変換器 5 演算処理部 6 メモリ 7 D/A変換器 8 R波検出器 A ドリフトキャンセル前のアンプ出力 B ドリフトキャンセル処理に基づくD/A出力 C ドリフトキャンセル後のアンプ出力 DESCRIPTION OF SYMBOLS 1 Differential amplifier 2 DC bias circuit 3 Main amplifier 4 A / D converter 5 Operation processing unit 6 Memory 7 D / A converter 8 R wave detector A Amplifier output before drift cancellation B D / A based on drift cancellation processing Output C Amplifier output after drift cancellation
Claims (2)
プを有する心電図解析装置のオートドリフトキャンセル
回路において、 前記心電図信号に基づいて、前記差動アンプに、当該差
動アンプの入力レンジ内に入るように、所定のタイミン
グにおける前記心電図信号の基線レベルに基づいて、バ
イアスを印加するバイアス手段を備えていることを特徴
とする心電図解析装置のオートドリフトキャンセル回
路。1. An auto-drift canceling circuit of an electrocardiogram analyzing apparatus having a differential amplifier for detecting and amplifying an electrocardiogram signal, wherein an auto-drift cancel circuit is provided in the differential amplifier based on the electrocardiogram signal within an input range of the differential amplifier. As you enter, the timing
A biasing means for applying a bias based on a baseline level of the electrocardiogram signal in the electrocardiogram analyzing apparatus.
電図信号を検出して増幅する差動アンプと、 前記心電図信号をA/D変換するためのA/D変換器
と、 該A/D変換器により得られた変換データからR波を検
出し、R−Rインターバルから心電図信号の基線時のタ
イミングを算出するR波検出部と、 該R波検出部で得られたタイミングにおける心電図信号
の基線レベルを、 前記差動アンプの入力レンジの中心にバイアスする直流
バイアス回路と、 該バイアス回路へのバイアス電圧を出力するD/A変換
器とを備えている ことを特徴とする心電図解析装置のオ
ートドリフトキャンセル回路。2. A heart derived from an electrode mounted on a subject
A differential amplifier for detecting and amplifying an electrogram signal, and an A / D converter for A / D converting the electrocardiogram signal
And an R wave is detected from the conversion data obtained by the A / D converter.
From the RR interval at the baseline of the ECG signal.
An R-wave detecting unit for calculating the timing, and an electrocardiogram signal at the timing obtained by the R-wave detecting unit
DC biasing the baseline level at the center of the input range of the differential amplifier
Bias circuit and D / A conversion for outputting a bias voltage to the bias circuit
Auto drift cancellation circuit electrocardiogram analysis apparatus characterized by comprising a vessel.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3284464A JP2765602B2 (en) | 1991-10-30 | 1991-10-30 | Auto drift cancellation circuit of ECG analyzer |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3284464A JP2765602B2 (en) | 1991-10-30 | 1991-10-30 | Auto drift cancellation circuit of ECG analyzer |
Publications (2)
Publication Number | Publication Date |
---|---|
JPH05115450A JPH05115450A (en) | 1993-05-14 |
JP2765602B2 true JP2765602B2 (en) | 1998-06-18 |
Family
ID=17678873
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP3284464A Expired - Lifetime JP2765602B2 (en) | 1991-10-30 | 1991-10-30 | Auto drift cancellation circuit of ECG analyzer |
Country Status (1)
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JP (1) | JP2765602B2 (en) |
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JPS57168011U (en) * | 1981-04-17 | 1982-10-22 | ||
JPH0648197B2 (en) * | 1984-09-06 | 1994-06-22 | 株式会社明電舍 | Zero correction sensor circuit |
JPS62177406A (en) * | 1986-01-31 | 1987-08-04 | Anritsu Corp | Displacement measuring instrument |
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1991
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JPH05115450A (en) | 1993-05-14 |
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